US4446871A - Optical analyzer for measuring a construction ratio between components in the living tissue - Google Patents

Optical analyzer for measuring a construction ratio between components in the living tissue Download PDF

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Publication number
US4446871A
US4446871A US06/216,526 US21652680A US4446871A US 4446871 A US4446871 A US 4446871A US 21652680 A US21652680 A US 21652680A US 4446871 A US4446871 A US 4446871A
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wavelength
light
wavelengths
hemoglobin
oxygen saturation
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US06/216,526
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Kenji Imura
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Minolta Co Ltd
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Minolta Co Ltd
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Assigned to MINOLTA CAMERA KABUSHIKI KAISHA, A CORP. OF JAPAN reassignment MINOLTA CAMERA KABUSHIKI KAISHA, A CORP. OF JAPAN ASSIGNMENT OF ASSIGNORS INTEREST. Assignors: IMURA KENJI
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    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated
    • G01N21/25—Colour; Spectral properties, i.e. comparison of effect of material on the light at two or more different wavelengths or wavelength bands
    • G01N21/31—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry
    • G01N21/314—Investigating relative effect of material at wavelengths characteristic of specific elements or molecules, e.g. atomic absorption spectrometry with comparison of measurements at specific and non-specific wavelengths
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/145—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue
    • A61B5/1455—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters
    • A61B5/1459—Measuring characteristics of blood in vivo, e.g. gas concentration or pH-value ; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid or cerebral tissue using optical sensors, e.g. spectral photometrical oximeters invasive, e.g. introduced into the body by a catheter

Definitions

  • the present invention generally relates to an electrooptical analyzer, such as an oximeter, for measuring a construction ratio between known components in living tissue, and more particularly to a non-invasive analyzer for optically analyzing living tissue without injuring it.
  • an electrooptical analyzer such as an oximeter
  • the measured intensities of light are influenced not only by the absorption of the hemoglobin oxide and hemoglobin, but also by various noise factors. Therefore, it is generally necessary to remove such noise factors to provide a meaningful measurement.
  • the light reflected from the living tissue would also include an additional or multiplying white noise factor due to surface reflection and/or light scattering in the non-blood tissue. Such white noise factors are quite difficult to be satisfactorily avoided or removed.
  • the measured intensity would also be influenced by the relative movement of the probe to the living tissue.
  • the prior art is still seeking a simplified but accurate oximeter.
  • An object of the present invention is to provide an optical analyzer utilizing a novel concept of operation.
  • Another object of the present invention is to provide an optical analyzer capable of accurate measurement free from the influence of noise factors.
  • a further object of the present invention is to provide an optical analyzer of a reflection light measurement type.
  • a still additional object of the present invention is to provide an optical analyzer capable of measurement even when the living tissue moves relative to the probe.
  • the intensities of a source light, after contact with living tissue are measured at various wavelengths.
  • a wavelength ⁇ at which the intensity of light is equal to that of a predetermined standard wavelength ⁇ 0 is searched, since the searched wavelength ⁇ depends on a construction ratio to be measured, such as hemoglobin oxide, the value of the construction ratio can be ascertained.
  • FIG. 1 represents a partially cross sectional schematic elevation view of the optical components of an embodiment of the present invention
  • FIG. 2 represents a partially cross sectional schematic plane view of some optical components of FIG. 1;
  • FIG. 4 represents a time chart showing the operation of the circuit of FIG. 3;
  • band-pass filters interference filters
  • These interference filters are mounted on the periphery of a rotary disc 11 for selectively positioning one of the band-pass filters on the optical axis of collimator 9 at various angles to the optical axis as seen in FIG. 2.
  • the light After passing through one of band-pass filters 11a to 11f located on the optical axis, the light is made convergent toward photocell 13 by means of collimator 12.
  • Rotary disc 11 can be driven by motor 20 through pulleys 16 and 18 and belt 17. The angle of rotation of rotary disc 11 is monitored or detected by a rotary encoder 19.
  • a white reflector 21 of a standard reflectance is measured prior to the measurement of an object for the purposes of calibrating the output of the device with respect to the various wavelengths scanned by band-pass filters 11a to 11f since the output of the device can be influenced by variable factors in the device, such as the spectral characteristics of the light source or the photocell.
  • the light scattered through and reflected from the living tissue is detected at a standard wavelength by photocell 15 and at various other wavelengths by photocell 13 with the specific wavelength of light received by photocell 13 encoded by means of rotary encoder 19.
  • a part B 1 integrated within a time period, in which chopper 4 allows a light passage would include both a signal component and a noise component
  • a part B 2 integrated within another time period, in which light is blocked by chopper 4 would include only the noise component.
  • the part B 1 is successively stored by sample hold circuit 23 controlled by sampling signal 23a.
  • the part B 2 is successively stored by sample hold circuit 24 under the control of sampling signal 24a.
  • the output C of sample hold circuit 23 includes both signal and noise components, and the output D of sample hold circuit 24 a noise component only. Output D is subtracted from output C at a succeeding subtraction circuit 25 to form signal E in which the noise component is eliminated.
  • the output current of photocell 15, which receives the light of standard wavelength ⁇ 0 is processed through current voltage converter 26, integrating circuit 27, sample hold circuits 28 and 29 and subtraction circuit 30 to obtain signal J.
  • the output K alternatingly shows the light intensities at the standard wavelength ⁇ 0 (corresponding to the J signal) and at the scanning wavelength ⁇ (corresponding to the E signal) in response to a predetermined time sequence from multiplexer 31.
  • FIG. 5 represents a block diagram of a microcomputer constituting a digital part of the electric circuit for processing the output signal of the optical system and connected to the above-described analog part.
  • A-D converter 36 is for converting the components in analog signal K corresponding to standard wavelength ⁇ 0 and scanning wavelength ⁇ into digital signals D ⁇ 0 and D ⁇ , respectively.
  • A-D converter 36 as well as multiplexer 31 in FIG. 3 is controlled by CPU 38.
  • the microcomputer in FIG. 5 processes as its input data the digital signals D ⁇ 0 and D ⁇ , and a digital output of the rotary encoder 19 indicative of the scanning wavelength ⁇ .
  • ROM 40 previously stores the coordinates of the scanning wavelengths to be addressed by the output of rotary encoder 19 and the oxygen saturation values addressed by the number of a scanning wavelength.
  • the microcomputer further includes a Random Access Memory (RAM) 39, Input and Output ports 37 and 41, and a display 42 for indicating the output of the microcomputer.
  • RAM Random Access Memory
  • (ii) CPU 38 readw the output of the rotary encoder 19 indicative of the rotation of disc 11 to successively address the numbers or coordinates of the scanning wavelengths.
  • (D ⁇ )cal.k and (D ⁇ 0 )cal.k are correspondingly read and stored in predetermined areas of RAM 39 in the order of the number of the scanning wavelength, wherein “cal.” means “calibrating” and k represents the number of the scanning wavelength numbered from 1 to n. It is needless to say that (D ⁇ 0 )cal.k's are all equal for various k's.
  • the probe is applied to an object to be measured, such as living tissue.
  • CPU 38 reads (D ⁇ ) mes.k and (D ⁇ 0 )mes.k in the similar manner as in step (ii), wherein the "mes.” means “measuring” and k represents the number of scanning wavelength.
  • CPU 38 further obtains D k according to a process expressed by the following formula, which calibrates (D ⁇ )mes.k and (D ⁇ 0 )mes.k with (D ⁇ )cal.k and (D ⁇ 0 )cal.k and obtains a ratio between the values relating to wavelengths ⁇ and ⁇ 0 as follows: ##EQU1##
  • (v) CPU 38 stores every D k corresponding to each number of a scanning wavelength in predetermined storage areas of RAM 39, respectively.
  • the above embodiment searches a wavelength ⁇ having an intensity equal to that of the standard wavelength ⁇ 0 with respect to the light contacting the living tissue to determine an oxygen saturation value from the searched wavelength ⁇ by way of a previously calculated and stored relationship between the oxygen saturation value vs. a wavelength ⁇ having an intensity equal to that of the standard wavelength ⁇ 0 .
  • the interference filters 10 and 11a to 11f are used for the purpose of introducing into the optical system a sufficient light flux with a wide range of wavelength values.
  • the light of standard wavelength ⁇ 0 is measured in synchronization with the measurement of every scanning wavelength ⁇ for the purpose of cancelling all possible noise factors, which could be caused in cause of a measurement wherein the probe does not directly contact the skin surface of the living tissue.
  • the procedure of measuring the light of standard wavelength ⁇ 0 with respect to every scanning wavelength ⁇ is not necessary from a theoretical view of obtaining the necessary information of light intensity of standard wavelength ⁇ 0 since it is theoretically equal with respect to all scanning wavelengths.
  • a standard wavelength is not necessarily selected from wavelengths other than the scanning wavelengths, but can be from the scanning wavelengths.
  • two or more standard wavelengths can be selected (as described later) simply by modifying the software of the microcomputer without further complicating the optical system to obtain two or more standard wavelengths.
  • the measured intensity I ⁇ of light of a scanning wavelength ⁇ which is incident on the living tissue and reflected by or transmitted through the same is expressed as follows:
  • I 0 represents the intensity of the incident light (made identical irrespective of the wavelength
  • r represents the reflectance at the surface of the living tissue (which is regarded as constant irregardless of the wavelength);
  • a represents the ratio of the light intensity I 0 .r to the measured intensity
  • ⁇ HbO 2 ⁇ and ⁇ Hb ⁇ represent the light absorption coefficients of hemoglobin oxide and hemoglobin at wavelength ⁇ , respectively;
  • CHbO 2 and CHb represent the densities of hemoglobin oxide and hemoglobin, respectively;
  • ⁇ and C ⁇ represent the light absorption coefficient of a tissue other than hemoglobin oxide and hemoglobin in the blood layer (which is regarded as independent of the wavelength and includes the attenuation factor by scattering) and its density, respectively;
  • d represents the optical path length of the blood layer B.
  • the measured intensity I ⁇ 0 of light of a standard wavelength ⁇ 0 is expressed as follows:
  • the measured intensity I ⁇ 0 is as follows:
  • equation (3) can be modified as follows: ##EQU2## If 1is added to both terms of this equation, ##EQU3## which is identical with ##EQU4## From this equation, ##EQU5## The lefthand term of equation (6) is identical with the definition of the oxygen saturation. This means that the oxygen saturation can be expressed by values kHb ⁇ and kHbO 2 ⁇ which are defined in formula (4) and (5).
  • the oxygen saturation is generally measured in accordance with a procedure comprising the steps of:
  • curves ⁇ , ⁇ and ⁇ represent three kinds of different spectral absorption characteristics of hemoglobin with different oxygen saturations, 100 percent, 50 percent and 0 percent, respectively.
  • the spectral absorption characteristics specifically differ depending on the amount of oxygen saturation of hemoglobin.
  • the present invention recognizes the cyclic response of light absorption by various wavelengths and particularly the fact that two or more wavelengths will experience equal absorption for the same level of hemoglobin oxide and hemoglobin.
  • the wavelength ⁇ at which the absorption coefficient is equal to that of the standard wavelength 757 nm is 664 nm in case of curve ⁇ for oxygen saturation, 100%.
  • 700 nm and 708 nm are the wavelengths showing equal absorption coefficient to that of standard wavelength in cases of curves ⁇ (for oxygen saturation, 50%) and ⁇ (for oxygen saturation 0%), respectively.
  • the wavelength at which the light absorption coefficient is equal to that of the standard wavelength differs in accordance with the oxygen saturation.
  • the wavelength further depends only on the oxygen saturation irrespective of any additional or multiplying noise factors which could be included in the measured light.
  • oxygen saturation is known to be 100%.
  • the above wavelength and the oxygen saturation correspond to each other on an equal level of signal, irregardless of any white noise factors.
  • Equation (9) to (14) kHbO 2 ⁇ , kHbO 2 ⁇ ', kHb ⁇ , kHb ⁇ ', kx ⁇ and kx ⁇ ' are all known. Accordingly, the oxygen saturation can be calculated by equation (15), and the construction ratio between the hemoglobin oxide, hemoglobin and the third component X can be obtainable by equations (15) and (16).
  • one oxygen saturation value is exclusively determined when at least one wavelength having an intensity equal to that of at least one standard wavelength is found. Therefore, various oxygen saturation values can be previously calculated in accordance with equations (6) or (15) with respect to various wavelengths and stored in ROM as in the prior embodiment. In this case, oxygen saturation can be obtained by reading out the data stored in ROM by addressing ROM with the searched wavelength.
  • the present invention is, however, not limited to such an embodiment, but can be embodied by substituting, for the microcomputer having a ROM, a calculation circuit, which actually carries out the calculation of equation (6) or (15) with respect to each wavelength sequentially.
  • the results of the previously calculated oxygen saturation values for various wavelengths can be printed as a sheet or table of values and the person who is informed of the searched wavelength by the device is capable of reading the oxygen saturation from the table by himself. Further, the person who is informed of the searched wavelength by the device can manually calculate the oxygen saturation in accordance with equation (6) or (15) by the aid of a general calculator or computer.
  • the device of the present invention is not for providing the actual oxygen saturation, but rather for identifying a specific searched wavelength which can indicate the actual oxygen saturation.
  • optical system of the present invention is not limited to the above-described embodiments, wherein the wavelengths to be measured are sequentially scanned, but could incorporate an optical system wherein all the necessary wavelengths are simultaneously separated into spectra and simultaneously measured in intensity.
  • the present invention is not only applicable to an oximeter as in the preferred embodiment, but also to other devices for optically analyzing a construction ratio of a known component to another known component, including living tissue of various animals or plants.

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  • Physics & Mathematics (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Health & Medical Sciences (AREA)
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  • Measurement Of The Respiration, Hearing Ability, Form, And Blood Characteristics Of Living Organisms (AREA)
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US06/216,526 1980-01-25 1980-12-15 Optical analyzer for measuring a construction ratio between components in the living tissue Expired - Fee Related US4446871A (en)

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JP807080A JPS56104646A (en) 1980-01-25 1980-01-25 Optical analyzer for forming ratio of element contained in organism

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Cited By (203)

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Publication number Priority date Publication date Assignee Title
US4608990A (en) * 1983-09-12 1986-09-02 Elings Virgil B Measuring skin perfusion
US4570638A (en) 1983-10-14 1986-02-18 Somanetics Corporation Method and apparatus for spectral transmissibility examination and analysis
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